US20060093175A1 - Hearing-aid anchoring element - Google Patents
Hearing-aid anchoring element Download PDFInfo
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- US20060093175A1 US20060093175A1 US10/981,340 US98134004A US2006093175A1 US 20060093175 A1 US20060093175 A1 US 20060093175A1 US 98134004 A US98134004 A US 98134004A US 2006093175 A1 US2006093175 A1 US 2006093175A1
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- fixture
- threaded portion
- bone
- hearing aid
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
- H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
- H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
Definitions
- the present invention relates to an anchoring fixture for anchoring a direct bone-conduction hearing-aid to the skull bone.
- Bone conduction hearing aids are essential for the rehabilitation of patients suffering from hearing losses for which traditional hearing aids are insufficient.
- Direct bone conduction hearing aids have a vibrating transducer that transmits vibrations directly to a fixture anchored in the bone, i.e. the skin does not take part in the transmission of the vibrations from the vibrator to the fixture in the bone.
- the most common type of such devices consists of an external hearing aid with a vibrating transducer which, through a coupling, is connected to a skin-penetrating abutment that has an interconnection to a screw shaped fixture anchored in the skull bone.
- a direct bone conduction hearing aid system may however be designed in other ways.
- the fixture is usually made of titanium and is often designed with a flange to prevent the fixture from being pushed through the skull bone in case of a sudden accidental impact.
- a hole is first drilled in the bone. After that the fixture can be screwed into the hole directly since the fixture is traditionally equipped with cutting edges to prepare the thread in the bone.
- the bone shivers are collected in shiver spaces at the cutting edges on the fixture. If the bone is very hard, a screw tap may be used to prepare the thread or part of the thread before the fixture is inserted.
- the fixture is then integrated with the skull-bone. This process is called osseointegration. After around 3 months, the osseointegration is usually sufficiently strong so that the fixture can be loaded and used. To achieve a firm and stable anchoring for the hearing aid a strong osseointegration is essential.
- the fixture is anchored to the skull bone is determined by several factors such as the surface characteristics of the fixture, the mechanical design of the fixture and the area of the contact surface between the bone and the fixture.
- the osseointegration process it is also important that the fixture is stable in the bone during the first 3 months when the osseointegration is established. The initial stability of the fixture in the bone is therefore also important for a successful treatment.
- the shiver spaces, where the fixture is not in direct bone contact directly after fixture insertion, are also, after a successful osseointegration has taken place, filled with bone tissue that comes in direct contact with the fixture surface in these cavities.
- connection screw is usually placed through the abutment and then screwed into a threaded hole in the fixture. It is important that this connection screw is sufficiently big to ensure a strong fixation of the abutment.
- the thickness of the skull bone is usually between 3-5 mm and the thickness determines the appropriate length of the fixture.
- a wide fixture offers more contact with the bone but, on the other hand, if it is too wide and short it might be difficult to insert. Therefore, the diameter of the fixtures is usually in the range 3.5-5 mm.
- the pitch of the thread is often chosen to be in the range of 0.5 to 0.8 mm.
- Existing fixtures used for anchoring direct bone conduction hearing aids have a depth of the thread of only around 0.3 mm.
- the depth of the thread on existing fixtures is less than 10% of the maximum outer diameter of the threaded portion of the fixture which limits the possible area of the contact surface between the fixture and the bone and limits the strength of the anchoring in the bone.
- the drilled hole in the bone has to have a diameter which is quite close to the inner diameter of the thread. Otherwise, there would be a low initial stability of the fixture in the bone.
- a fixture When inserting a fixture in a hole that has a diameter which is quite close to the inner diameter of the thread quite a lot of bone shivers are generated. These bone shivers must be collected mainly in the shivers space cavities at the cutting edges on the fixture. Therefore, these shiver space cavities must be quite big.
- the fixture since the fixture includes an inner hole for the connection of, for example, an abutment connection screw, it may be difficult to do the shiver spaces sufficiently deep without interfering with the inner hole in the fixture. This compromise leads to a less optimal design of existing fixtures.
- Existing fixtures used for anchoring direct bone conduction hearing aids have a simple quite smooth machined titanium surface.
- the existing fixtures also have a very thin titanium oxide layer on its surface. These surface characteristics do not present the optimal properties to achieve maximum osseointegration.
- the anchoring element of the present invention provides an effective solution to the above-outlined problems with existing fixtures used for anchoring direct bone conduction hearing aids.
- the thread pitch of the fixture of the present invention is in the range 0.5 to 0.8 mm. This size of the pitch has shown to be optimal for osseointegrated fixtures from a biomechanical point of view.
- the fixture of the present invention has a depth of the thread that is at least 10% of the maximum diameter of the threaded portion of the fixture.
- the depth of the threaded portion is however not greater than 20% of the maximum diameter of the thread of the fixture.
- a fixture having a thread that is at least 10% of the maximum diameter of the threaded portion of the fixture is inserted in a drilled hole in the bone where the drilled hole has a significantly larger diameter than the inner diameter of the thread, without compromising the initial stability of the fixture compared to existing fixtures.
- Another advantage with the fixture of the present invention is that if it is inserted into a drilled hole in the bone which has significantly larger diameter than the inner diameter of the thread, there will be a space between the bottom of the thread grove on the fixture and the bone, when it has been inserted into the hole in the bone.
- the depth of the threaded portion to less than 20% of the maximum diameter of the threaded portion of the fixture is essential so that the thread profile of the fixture does not become too weak from a mechanical point of view. A thread deeper than this might also complicate the manufacturing procedure for the fixture. By keeping the depth of the threaded portion to less than 20% of the maximum diameter of the threaded portion of the fixture there will also be sufficient volume in the center of the fixture to accommodate a sufficient inner hole for attaching the hearing aid abutment in a stable way.
- the unique advantages of the fixture of the present invention are achieved by having a thread depth that is specifically in the range 10% to 20% of the maximum diameter of the threaded portion of the fixture.
- the advantages of this on both macroscopic and microscopic level offer significant clinical advantages for patients in need of direct bone conduction hearing aid.
- the anchoring of the fixture is significantly stronger and therefore the risk for the fixture to become loose is reduced.
- the important advantages mentioned above have never been achieved and could never have been achieved with existing fixture designs.
- the present invention solves several drawbacks with existing solutions and significantly improves the clinical outcome of the rehabilitation of patients in need for a direct bone conduction hearing aid.
- the fixture of the present invention has at least one cutting edge and each cutting edge may have an adjacent cavity where bone shivers may be collected. If there are more cavities the volume of each cavity may be less than if there are fewer cavities.
- the cavities on a fixture with more than one cavity do not necessarily have to be identical although this may be a preferred solution. To define the total volume of these cavities it may be assumed that the fixture is manufactured in a machining process although the present invention is not limited to this type of manufacturing process.
- the total volume of the cavities may then be defined as: the total volume of a fixture where the machining procedure for creating the cavities has not been performed, minus the total volume of the same fixture but where the machining procedure for creating the cavities has been completed. Another way of describing this volume is to assume that the total volume of the cavities is the total volume of the fixture material that is be removed from the fixture when these cavities are created in a machining process if this machining process is done as the last machining process in the manufacturing of the final shape of the fixture i.e. after the creation of the thread.
- the total volume of the cavities may be greater than 50% of the cut off bone volume when the fixture has been screwed into a hole in the bone where the hole has a diameter which is 10% greater than the inner diameter of the thread. This provides a sufficient collection of bone shivers in the cavities since bone shivers may in this case also be collected along the thread as described above.
- the present invention involves a preparation of the hole in the bone using a drill with a diameter that is at least 10% wider and not more than 20% wider than the inner diameter of the thread of the fixture.
- a drill with a diameter that is at least 10% wider and not more than 20% wider than the inner diameter of the thread of the fixture.
- the amount of bone shivers as well as the insertion torque for the fixture is limited. Since the inner diameter of the thread is smaller than the diameter of the drilled hole, bone shivers can also be collected in the space between the bone and the inner diameter of the thread of the fixture. In this way, the amount of bone shivers that need to be collected in the cavities on the fixture can be kept down.
- a hole with a diameter greater than 20% wider than the inner diameter of the thread of the fixture may lead to a poor initial stability of the fixture.
- the threaded portion may have relieving surfaces behind the cutting edges. The relieving reduces the friction between the fixture and the bone at the part of the fixture that follows the cutting edge when the fixture is screwed into the bone.
- the threaded portion may have a relieving portion at its distal end and where this relieving portion has a slightly smaller outer diameter of the thread than the maximum outer diameter of the threaded portion. This relieving reduces the friction between the fixture and the bone at the distal part of the threaded portion and therefore contributes to a lower insertion torque when inserting the fixture in the bone.
- the fixture has a titanium oxide layer with a thickness of at least 100 nm on the surface of the threaded portion.
- a titanium oxide layer with a thickness of at least 100 nm on the surface of the threaded portion.
- the surface of the threaded portion will show improved osseointegration properties since titanium oxide is a biomaterial that interacts with the living bone tissue in a way that contributes to a strong osseointegration. Due to the fact that a fixture anchored in the skull bone is quite short, it is especially important for patients in need for a direct bone conduction hearing aid, that the strength of the osseointegration bond between the fixture and the bone tissue is high. With a strong osseointegration the risk for clinical complications for these patients is significantly reduced.
- the porous titanium oxide has a porous structure since this further improves the osseointegration properties by allowing a bone tissue to interact even further with the titanium oxide.
- the titanium oxide on the fixture surface may well include or be covered by other chemical or biological substances to even further improve the osseointegration.
- the surface of the threaded portion of the fixture may have an average surface roughness S a where 1 ⁇ m ⁇ S a ⁇ 3 ⁇ m. This surface roughness may increase the contact surface between the fixture and the bone tissue and will further contribute to an improved strength of the osseointegration of the fixture in the bone.
- the fixture of the present invention presents at least one groove extending at least one turn on the side of the flange facing the threaded portion.
- This arrangement will acts as a micro thread in contact with the bone. Since bone resorbtion starts in the periphery of the flange, this arrangement will hinders the bone resorbtion under the flange. This is a similar effect as the well know effect of the thread of the threaded portion for existing fixtures, where the The thread is hindering the bone resorbtion from going further down along the threaded portion in contra distal direction.
- FIG. 1 is a side view of the hearing aid of the present invention built into an example of a direct bone conduction hearing aid system
- FIG. 2 is a cross-sectional side view of a preferred embodiment of the fixture of the present invention.
- FIG. 3 is a cross-sectional bottom view of the embodiment along line 3 - 3 shown in FIG. 2 ;
- FIG. 4 is a perspective view of the fixture shown in FIG. 2 ;
- FIG. 5 is a flowchart of a preferred method of using the fixture of the present invention.
- FIG. 1 is a side view of an illustrative example of a direct bone conduction hearing aid system 100 that has an abutment 102 with a fixture 104 that is screwed into a skull bone 106 of a user.
- a hearing-aid device 108 converts sound into vibrations and the vibrations is transferred to the skull bone 106 .
- FIG. 2 is a cross-sectional side view and FIG. 4 is a perspective view of a preferred embodiment of the fixture 104 .
- the fixture 104 has a threaded portion 110 having a maximum outer diameter d 1 and an inner diameter d 2 .
- the thread has a depth d t and a thread pitch t p .
- the fixture has a conical outer portion 112 to facilitate the insertion of the fixture 104 into a hole in the skull bone 106 .
- An upper end of the fixture 104 has a radially outwardly protruding flange 114 with a diameter d 3 to prevent the fixture 104 from being pushed into the skull.
- the diameter d 3 is greater than the diameter d 2 .
- An axial extension 130 has an axial threaded inner hole 116 defined therein.
- the hole 116 extends from an upper surface 132 of the extension to a conical shaped bottom 134 .
- the hole may be used for receiving, for example, a connection screw for connecting the fixture 104 to the abutment 102 .
- the side of the flange 114 facing the threaded portion 110 has grooves 136 .
- the conical outer end 112 of the fixture 104 has cutting edges 118 .
- the cutting edges 118 have cavities 120 defined therein.
- the cutting edges 118 may be used to cut a thread in the bone as the fixture 104 is screwed into the skull bone 106 .
- the bone shivers from the skull bone 106 may then be collected in the cavities 120 that provide a space for the shivers.
- the thread has a thread groove 121 defined therein.
- the threaded portion 110 has a relieving portion 122 at the distal end and positioned below the flange 114 but above the outer end 112 .
- the distal direction is represented by the arrow (D).
- the relieving portion 122 has an outer diameter d 4 that, preferably, is smaller than the maximum outer diameter d 1 of the threaded portion 110 .
- FIG. 3 is a cross-sectional bottom view of the embodiment showed along line 3 - 3 in FIG. 2 .
- the fixture has relieving surfaces 124 abc behind each of the cutting edges 118 abc , respectively.
- the cutting edges 118 abc have adjacent cavities 120 abc , respectively. As the cutting edges 118 cuts into the skull bone 106 when outer end 112 is screwed into the skull bone, the bone shiver may be deposited into the cavities 120 and relieving surfaces 124 .
- FIG. 5 is a flow chart of a preferred embodiment and illustrates a preferred insertion method for inserting the fixture in the skull bone.
- the method 200 has a providing step 202 for providing a drill that has a diameter that is 10-20% wider than the diameter d 2 of the fixture.
- a preparation step 204 a hole is prepared in the skull bone by drilling the hole with the drill.
- a fixture providing step 206 a direct bone conduction hearing-aid fixture is provided that has a thread depth d t where d t is greater than 10% of the diameter d 1 .
- the fixture is screwed into the hole in the skull bone.
- an osseointegration step 210 the screw is left in the skull bone until the fixture is fully osseointegrated with the skull bone.
Abstract
Description
- The present invention relates to an anchoring fixture for anchoring a direct bone-conduction hearing-aid to the skull bone.
- Bone conduction hearing aids are essential for the rehabilitation of patients suffering from hearing losses for which traditional hearing aids are insufficient. Direct bone conduction hearing aids have a vibrating transducer that transmits vibrations directly to a fixture anchored in the bone, i.e. the skin does not take part in the transmission of the vibrations from the vibrator to the fixture in the bone. The most common type of such devices consists of an external hearing aid with a vibrating transducer which, through a coupling, is connected to a skin-penetrating abutment that has an interconnection to a screw shaped fixture anchored in the skull bone. A direct bone conduction hearing aid system may however be designed in other ways.
- The fixture is usually made of titanium and is often designed with a flange to prevent the fixture from being pushed through the skull bone in case of a sudden accidental impact.
- To insert the fixture into the skull bone a hole is first drilled in the bone. After that the fixture can be screwed into the hole directly since the fixture is traditionally equipped with cutting edges to prepare the thread in the bone. The bone shivers are collected in shiver spaces at the cutting edges on the fixture. If the bone is very hard, a screw tap may be used to prepare the thread or part of the thread before the fixture is inserted. The fixture is then integrated with the skull-bone. This process is called osseointegration. After around 3 months, the osseointegration is usually sufficiently strong so that the fixture can be loaded and used. To achieve a firm and stable anchoring for the hearing aid a strong osseointegration is essential. How well the fixture is anchored to the skull bone is determined by several factors such as the surface characteristics of the fixture, the mechanical design of the fixture and the area of the contact surface between the bone and the fixture. For the osseointegration process to be successful it is also important that the fixture is stable in the bone during the first 3 months when the osseointegration is established. The initial stability of the fixture in the bone is therefore also important for a successful treatment.
- The shiver spaces, where the fixture is not in direct bone contact directly after fixture insertion, are also, after a successful osseointegration has taken place, filled with bone tissue that comes in direct contact with the fixture surface in these cavities.
- To fixate the skin penetrating abutment to the fixture a connection screw is usually placed through the abutment and then screwed into a threaded hole in the fixture. It is important that this connection screw is sufficiently big to ensure a strong fixation of the abutment.
- The thickness of the skull bone is usually between 3-5 mm and the thickness determines the appropriate length of the fixture. A wide fixture offers more contact with the bone but, on the other hand, if it is too wide and short it might be difficult to insert. Therefore, the diameter of the fixtures is usually in the range 3.5-5 mm. To ensure that the biomechanical and osseointegration properties of the fixture are functioning well, the pitch of the thread is often chosen to be in the range of 0.5 to 0.8 mm.
- Existing fixtures used for anchoring direct bone conduction hearing aids have a depth of the thread of only around 0.3 mm. The depth of the thread on existing fixtures is less than 10% of the maximum outer diameter of the threaded portion of the fixture which limits the possible area of the contact surface between the fixture and the bone and limits the strength of the anchoring in the bone.
- Due to the small depth of the thread on existing fixtures, the drilled hole in the bone has to have a diameter which is quite close to the inner diameter of the thread. Otherwise, there would be a low initial stability of the fixture in the bone. When inserting a fixture in a hole that has a diameter which is quite close to the inner diameter of the thread quite a lot of bone shivers are generated. These bone shivers must be collected mainly in the shivers space cavities at the cutting edges on the fixture. Therefore, these shiver space cavities must be quite big. However, since the fixture includes an inner hole for the connection of, for example, an abutment connection screw, it may be difficult to do the shiver spaces sufficiently deep without interfering with the inner hole in the fixture. This compromise leads to a less optimal design of existing fixtures.
- Existing fixtures used for anchoring direct bone conduction hearing aids have a simple quite smooth machined titanium surface. The existing fixtures also have a very thin titanium oxide layer on its surface. These surface characteristics do not present the optimal properties to achieve maximum osseointegration.
- Existing fixtures has also a flat surface on the side of the flange facing the threaded portion. A common problem that occurs when the fixture has osseointegrate is that the bone closest to the flange is resorbed which gives a lower stability of the fixture in the bone.
- Due to the less optimal macroscopic and microscopic properties of existing fixtures, patients experience several clinical problems. One problem is fixtures that do not osseointegrate properly from the beginning so that the patient has to come back to the hospital to have a new surgical procedure performed. Another problem is that fixtures that have osseointegrated with the bone become loose in the bone due to mechanical load on the fixture. The mechanical load may for example be pulling or rotational forces. In this case a new surgery has also to be performed. The problem with existing fixtures is that the design and the thread profiles have mainly been copied from standard mechanical screws rather than being designed for its clinical, biomechanical and osseointeration purpose. Designing an anchoring system for a lifelong medical rehabilitation requires paying attention to the biological implant interactions with the bone tissue. This is a demanding development work where the lack of optimized key design parameters may lead to the need for patients coming in for surgical procedures, which could have been avoided if the fixture design would have been more favorable from a biomechanical and biological point of view. The existing fixture designs have and have always had problems with for example fixtures coming loose from the skull bone, due to an insufficient interaction with the bone tissue.
- There is a need for a more effective anchoring and fixture arrangements that do not have the deficiencies described above.
- The anchoring element of the present invention provides an effective solution to the above-outlined problems with existing fixtures used for anchoring direct bone conduction hearing aids. The thread pitch of the fixture of the present invention is in the range 0.5 to 0.8 mm. This size of the pitch has shown to be optimal for osseointegrated fixtures from a biomechanical point of view.
- The fixture of the present invention has a depth of the thread that is at least 10% of the maximum diameter of the threaded portion of the fixture. The depth of the threaded portion is however not greater than 20% of the maximum diameter of the thread of the fixture. By designing the depth of the thread in this interval, several significant and surprising advantages can be achieved for a fixture intended to be used for anchoring direct bone conduction hearing aids. The improvements are both on the microscopic and the macroscopic level. On a microscopic level, the increased surface offers an increased contact surface between the bone tissue and the fixture and this will contribute to a higher removal torque if forces directed to screw out the fixture from the bone is applied to the fixture when the fixture is osseointegrated. On a macroscopic level, the increased depth of the thread results in a firmer grip in the bone if trying to pull the fixture out of the hole.
- By keeping the thread depth in this range significant improvements to the surgical procedure are achieved. A fixture having a thread that is at least 10% of the maximum diameter of the threaded portion of the fixture is inserted in a drilled hole in the bone where the drilled hole has a significantly larger diameter than the inner diameter of the thread, without compromising the initial stability of the fixture compared to existing fixtures. Another advantage with the fixture of the present invention is that if it is inserted into a drilled hole in the bone which has significantly larger diameter than the inner diameter of the thread, there will be a space between the bottom of the thread grove on the fixture and the bone, when it has been inserted into the hole in the bone. This allows bone shivers to be collected in a helix-shaped space along the thread of the fixture in the bottom of the thread groove and contributes to the accommodation of the cut off and compressed bone material. The insertion of the fixture into a larger hole in the bone had the surprising result of requiring a further reduced amount of torque when the fixture is inserted into the bone. One reason for this is the ability of the fixture to collect bone material along the thread groove.
- Keeping the depth of the threaded portion to less than 20% of the maximum diameter of the threaded portion of the fixture is essential so that the thread profile of the fixture does not become too weak from a mechanical point of view. A thread deeper than this might also complicate the manufacturing procedure for the fixture. By keeping the depth of the threaded portion to less than 20% of the maximum diameter of the threaded portion of the fixture there will also be sufficient volume in the center of the fixture to accommodate a sufficient inner hole for attaching the hearing aid abutment in a stable way.
- The unique advantages of the fixture of the present invention are achieved by having a thread depth that is specifically in the range 10% to 20% of the maximum diameter of the threaded portion of the fixture. The advantages of this on both macroscopic and microscopic level offer significant clinical advantages for patients in need of direct bone conduction hearing aid. The anchoring of the fixture is significantly stronger and therefore the risk for the fixture to become loose is reduced.
- The important advantages mentioned above have never been achieved and could never have been achieved with existing fixture designs. The present invention solves several drawbacks with existing solutions and significantly improves the clinical outcome of the rehabilitation of patients in need for a direct bone conduction hearing aid.
- The fixture of the present invention has at least one cutting edge and each cutting edge may have an adjacent cavity where bone shivers may be collected. If there are more cavities the volume of each cavity may be less than if there are fewer cavities. The cavities on a fixture with more than one cavity do not necessarily have to be identical although this may be a preferred solution. To define the total volume of these cavities it may be assumed that the fixture is manufactured in a machining process although the present invention is not limited to this type of manufacturing process.
- The total volume of the cavities may then be defined as: the total volume of a fixture where the machining procedure for creating the cavities has not been performed, minus the total volume of the same fixture but where the machining procedure for creating the cavities has been completed. Another way of describing this volume is to assume that the total volume of the cavities is the total volume of the fixture material that is be removed from the fixture when these cavities are created in a machining process if this machining process is done as the last machining process in the manufacturing of the final shape of the fixture i.e. after the creation of the thread.
- In the present invention, the total volume of the cavities may be greater than 50% of the cut off bone volume when the fixture has been screwed into a hole in the bone where the hole has a diameter which is 10% greater than the inner diameter of the thread. This provides a sufficient collection of bone shivers in the cavities since bone shivers may in this case also be collected along the thread as described above.
- In a preferred procedure, the present invention involves a preparation of the hole in the bone using a drill with a diameter that is at least 10% wider and not more than 20% wider than the inner diameter of the thread of the fixture. In this way, the amount of bone shivers as well as the insertion torque for the fixture is limited. Since the inner diameter of the thread is smaller than the diameter of the drilled hole, bone shivers can also be collected in the space between the bone and the inner diameter of the thread of the fixture. In this way, the amount of bone shivers that need to be collected in the cavities on the fixture can be kept down. A hole with a diameter greater than 20% wider than the inner diameter of the thread of the fixture may lead to a poor initial stability of the fixture.
- In a preferred embodiment, the threaded portion may have relieving surfaces behind the cutting edges. The relieving reduces the friction between the fixture and the bone at the part of the fixture that follows the cutting edge when the fixture is screwed into the bone.
- In another preferred embodiment, the threaded portion may have a relieving portion at its distal end and where this relieving portion has a slightly smaller outer diameter of the thread than the maximum outer diameter of the threaded portion. This relieving reduces the friction between the fixture and the bone at the distal part of the threaded portion and therefore contributes to a lower insertion torque when inserting the fixture in the bone.
- In a preferred embodiment the fixture has a titanium oxide layer with a thickness of at least 100 nm on the surface of the threaded portion. By having a thicker titanium oxide layer, the surface of the threaded portion will show improved osseointegration properties since titanium oxide is a biomaterial that interacts with the living bone tissue in a way that contributes to a strong osseointegration. Due to the fact that a fixture anchored in the skull bone is quite short, it is especially important for patients in need for a direct bone conduction hearing aid, that the strength of the osseointegration bond between the fixture and the bone tissue is high. With a strong osseointegration the risk for clinical complications for these patients is significantly reduced.
- In a preferred embodiment, the porous titanium oxide has a porous structure since this further improves the osseointegration properties by allowing a bone tissue to interact even further with the titanium oxide. The titanium oxide on the fixture surface may well include or be covered by other chemical or biological substances to even further improve the osseointegration.
- In a preferred embodiment of the present invention, the surface of the threaded portion of the fixture may have an average surface roughness Sa where 1 μm≦Sa≦3 μm. This surface roughness may increase the contact surface between the fixture and the bone tissue and will further contribute to an improved strength of the osseointegration of the fixture in the bone.
- In a preferred embodiment the fixture of the present invention presents at least one groove extending at least one turn on the side of the flange facing the threaded portion. This arrangement will acts as a micro thread in contact with the bone. Since bone resorbtion starts in the periphery of the flange, this arrangement will hinders the bone resorbtion under the flange. This is a similar effect as the well know effect of the thread of the threaded portion for existing fixtures, where the The thread is hindering the bone resorbtion from going further down along the threaded portion in contra distal direction.
-
FIG. 1 is a side view of the hearing aid of the present invention built into an example of a direct bone conduction hearing aid system; -
FIG. 2 is a cross-sectional side view of a preferred embodiment of the fixture of the present invention; -
FIG. 3 is a cross-sectional bottom view of the embodiment along line 3-3 shown inFIG. 2 ; -
FIG. 4 is a perspective view of the fixture shown inFIG. 2 ; and -
FIG. 5 is a flowchart of a preferred method of using the fixture of the present invention. -
FIG. 1 is a side view of an illustrative example of a direct bone conductionhearing aid system 100 that has anabutment 102 with afixture 104 that is screwed into askull bone 106 of a user. A hearing-aid device 108 converts sound into vibrations and the vibrations is transferred to theskull bone 106. -
FIG. 2 is a cross-sectional side view andFIG. 4 is a perspective view of a preferred embodiment of thefixture 104. Thefixture 104 has a threadedportion 110 having a maximum outer diameter d1 and an inner diameter d2. The thread has a depth dt and a thread pitch tp. The fixture has a conicalouter portion 112 to facilitate the insertion of thefixture 104 into a hole in theskull bone 106. - An upper end of the
fixture 104 has a radially outwardly protrudingflange 114 with a diameter d3 to prevent thefixture 104 from being pushed into the skull. Preferably, the diameter d3 is greater than the diameter d2. Anaxial extension 130 has an axial threadedinner hole 116 defined therein. Thehole 116 extends from anupper surface 132 of the extension to a conical shapedbottom 134. The hole may be used for receiving, for example, a connection screw for connecting thefixture 104 to theabutment 102. The side of theflange 114 facing the threadedportion 110 has grooves 136. The conicalouter end 112 of thefixture 104 has cuttingedges 118. The cutting edges 118 havecavities 120 defined therein. The cutting edges 118 may be used to cut a thread in the bone as thefixture 104 is screwed into theskull bone 106. The bone shivers from theskull bone 106 may then be collected in thecavities 120 that provide a space for the shivers. The thread has athread groove 121 defined therein. - The threaded
portion 110 has a relievingportion 122 at the distal end and positioned below theflange 114 but above theouter end 112. The distal direction is represented by the arrow (D). The relievingportion 122 has an outer diameter d4 that, preferably, is smaller than the maximum outer diameter d1 of the threadedportion 110. -
FIG. 3 is a cross-sectional bottom view of the embodiment showed along line 3-3 inFIG. 2 . The fixture has relievingsurfaces 124 abc behind each of the cutting edges 118 abc, respectively. The cutting edges 118 abc haveadjacent cavities 120 abc, respectively. As the cutting edges 118 cuts into theskull bone 106 whenouter end 112 is screwed into the skull bone, the bone shiver may be deposited into thecavities 120 and relievingsurfaces 124. -
FIG. 5 is a flow chart of a preferred embodiment and illustrates a preferred insertion method for inserting the fixture in the skull bone. Themethod 200 has a providing step 202 for providing a drill that has a diameter that is 10-20% wider than the diameter d2 of the fixture. In apreparation step 204, a hole is prepared in the skull bone by drilling the hole with the drill. In afixture providing step 206, a direct bone conduction hearing-aid fixture is provided that has a thread depth dt where dt is greater than 10% of the diameter d1. In a screwingstep 208, the fixture is screwed into the hole in the skull bone. In anosseointegration step 210, the screw is left in the skull bone until the fixture is fully osseointegrated with the skull bone. - While the present invention has been described in accordance with preferred compositions and embodiments, it is to be understood that certain substitutions and alterations may be made thereto without departing from the spirit and scope of the following claims.
Claims (13)
Priority Applications (10)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/981,340 US7116794B2 (en) | 2004-11-04 | 2004-11-04 | Hearing-aid anchoring element |
DE05818388T DE05818388T1 (en) | 2004-11-04 | 2005-11-01 | ANCHORING ELEMENT FOR HEARING EQUIPMENT |
EP05818388A EP1820368B1 (en) | 2004-11-04 | 2005-11-01 | Hearing-aid anchoring element |
DK05818388.0T DK1820368T3 (en) | 2004-11-04 | 2005-11-01 | Anchor element for hearing aid |
DE602005022104T DE602005022104D1 (en) | 2004-11-04 | 2005-11-01 | ANCHORING ELEMENT FOR HEARING EQUIPMENT |
PCT/US2005/039419 WO2006052527A2 (en) | 2004-11-04 | 2005-11-01 | Hearing-aid anchoring element |
AU2005305125A AU2005305125B2 (en) | 2004-11-04 | 2005-11-01 | Hearing-aid anchoring element |
CN200580038191XA CN101057525B (en) | 2004-11-04 | 2005-11-01 | Hearing-aid anchoring element |
AT05818388T ATE472904T1 (en) | 2004-11-04 | 2005-11-01 | ANCHORING ELEMENT FOR HEARING AIDS |
US11/351,505 US20060126874A1 (en) | 2004-11-04 | 2006-02-10 | Hearing-aid anchoring element |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/981,340 US7116794B2 (en) | 2004-11-04 | 2004-11-04 | Hearing-aid anchoring element |
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US11/351,505 Continuation-In-Part US20060126874A1 (en) | 2004-11-04 | 2006-02-10 | Hearing-aid anchoring element |
Publications (2)
Publication Number | Publication Date |
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US20060093175A1 true US20060093175A1 (en) | 2006-05-04 |
US7116794B2 US7116794B2 (en) | 2006-10-03 |
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US10/981,340 Active 2025-02-15 US7116794B2 (en) | 2004-11-04 | 2004-11-04 | Hearing-aid anchoring element |
US11/351,505 Abandoned US20060126874A1 (en) | 2004-11-04 | 2006-02-10 | Hearing-aid anchoring element |
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US11/351,505 Abandoned US20060126874A1 (en) | 2004-11-04 | 2006-02-10 | Hearing-aid anchoring element |
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US (2) | US7116794B2 (en) |
EP (1) | EP1820368B1 (en) |
CN (1) | CN101057525B (en) |
AT (1) | ATE472904T1 (en) |
AU (1) | AU2005305125B2 (en) |
DE (2) | DE05818388T1 (en) |
DK (1) | DK1820368T3 (en) |
WO (1) | WO2006052527A2 (en) |
Cited By (7)
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WO2008143575A1 (en) * | 2007-05-24 | 2008-11-27 | Cochlear Limited | Anchoring element |
WO2008143574A1 (en) * | 2007-05-24 | 2008-11-27 | Cochlear Limited | Implant abutment |
US20090023109A1 (en) * | 2007-07-20 | 2009-01-22 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US20150215696A1 (en) * | 2014-01-30 | 2015-07-30 | Cochlear Limited | Bone conduction implant |
USD955578S1 (en) | 2019-10-25 | 2022-06-21 | Cochlear Limited | Implant tool |
EP4017030A1 (en) | 2020-12-18 | 2022-06-22 | CADskills | Device for coupling a bone conduction vibrator |
USD982745S1 (en) | 2019-10-25 | 2023-04-04 | Cochlear Limited | Implant tool |
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US8401213B2 (en) * | 2008-03-31 | 2013-03-19 | Cochlear Limited | Snap-lock coupling system for a prosthetic device |
US8737649B2 (en) * | 2008-03-31 | 2014-05-27 | Cochlear Limited | Bone conduction device with a user interface |
US20090321145A1 (en) * | 2008-06-26 | 2009-12-31 | Kennametal Inc. | Threaded nozzle for a cutter bit |
DE102009014771A1 (en) * | 2009-03-25 | 2010-09-30 | Cochlear Ltd., Lane Cove | Percutaneous hearing aid implant for permanent anchoring in skull bone of patient, has counter bearing provided with outer surface, where antibacterial coating is applied on inner part of bearing and/or bone fastener and/or surface of screw |
US8242444B2 (en) * | 2009-04-15 | 2012-08-14 | Exelis, Inc. | Ganged focus mechanism for an optical device |
EP2252079A1 (en) * | 2009-05-14 | 2010-11-17 | Oticon A/S | Bone anchored bone conductive hearing aid |
US8594356B2 (en) * | 2010-04-29 | 2013-11-26 | Cochlear Limited | Bone conduction device having limited range of travel |
US20120294466A1 (en) * | 2011-05-18 | 2012-11-22 | Stefan Kristo | Temporary anchor for a hearing prosthesis |
US20130130200A1 (en) * | 2011-10-21 | 2013-05-23 | Milan Djordjevic | Flatbed Dental Implant |
US20140121450A1 (en) * | 2012-07-16 | 2014-05-01 | Sophono, Inc. | Magnetic Abutment Systems, Devices, Components and Methods for Bone Conduction Hearing Aids |
US10893933B2 (en) | 2017-02-24 | 2021-01-19 | James Jastifer | Tissue anchors, kits, and associated methods |
WO2020129021A1 (en) * | 2018-12-21 | 2020-06-25 | Cochlear Limited | Advanced bone conduction implant |
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- 2005-11-01 WO PCT/US2005/039419 patent/WO2006052527A2/en active Application Filing
- 2005-11-01 CN CN200580038191XA patent/CN101057525B/en active Active
- 2005-11-01 DE DE05818388T patent/DE05818388T1/en active Pending
- 2005-11-01 DK DK05818388.0T patent/DK1820368T3/en active
- 2005-11-01 DE DE602005022104T patent/DE602005022104D1/en active Active
- 2005-11-01 AT AT05818388T patent/ATE472904T1/en not_active IP Right Cessation
- 2005-11-01 EP EP05818388A patent/EP1820368B1/en active Active
- 2005-11-01 AU AU2005305125A patent/AU2005305125B2/en active Active
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US6663634B2 (en) * | 1999-02-04 | 2003-12-16 | Synthes (U.S.A.) | Bone screw |
US20030176866A1 (en) * | 2000-07-12 | 2003-09-18 | Patrik Westerkull | Anchoring element |
US6685728B2 (en) * | 2002-01-25 | 2004-02-03 | Stryker Endoscopy | Threaded suture anchor and method of use |
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US9005202B2 (en) | 2007-05-24 | 2015-04-14 | Cochlear Limited | Implant abutment |
WO2008143574A1 (en) * | 2007-05-24 | 2008-11-27 | Cochlear Limited | Implant abutment |
US10848882B2 (en) | 2007-05-24 | 2020-11-24 | Cochlear Limited | Implant abutment |
US9888329B2 (en) | 2007-05-24 | 2018-02-06 | Cochlear Limited | Implant abutment |
WO2008143575A1 (en) * | 2007-05-24 | 2008-11-27 | Cochlear Limited | Anchoring element |
US20100209873A1 (en) * | 2007-05-24 | 2010-08-19 | Cochlear Limited | Anchoring element |
US20100249784A1 (en) * | 2007-05-24 | 2010-09-30 | Cochlear Limited | Implant abutment |
US8454668B2 (en) | 2007-05-24 | 2013-06-04 | Cochlear Limited | Anchoring element |
US20160038202A1 (en) * | 2007-07-20 | 2016-02-11 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US20090023109A1 (en) * | 2007-07-20 | 2009-01-22 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US11882409B2 (en) * | 2007-07-20 | 2024-01-23 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US9173042B2 (en) * | 2007-07-20 | 2015-10-27 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US20090082817A1 (en) * | 2007-07-20 | 2009-03-26 | Cochlear Limited | Coupling apparatus for a bone anchored hearing device |
US9838807B2 (en) * | 2007-07-20 | 2017-12-05 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
WO2009015102A1 (en) * | 2007-07-20 | 2009-01-29 | Cochlear Americas | Bone anchor fixture for a medical prosthesis |
US10750298B2 (en) | 2007-07-20 | 2020-08-18 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US10750297B2 (en) * | 2007-07-20 | 2020-08-18 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
US20210058721A1 (en) * | 2007-07-20 | 2021-02-25 | Lars Jinton | Bone anchor fixture for a medical prosthesis |
US20150215696A1 (en) * | 2014-01-30 | 2015-07-30 | Cochlear Limited | Bone conduction implant |
US11240613B2 (en) * | 2014-01-30 | 2022-02-01 | Cochlear Limited | Bone conduction implant |
US20220159391A1 (en) * | 2014-01-30 | 2022-05-19 | Goran Bjorn | Bone conduction implant |
WO2015114591A1 (en) * | 2014-01-30 | 2015-08-06 | Cochlear Limited | Bone conduction implant |
USD955578S1 (en) | 2019-10-25 | 2022-06-21 | Cochlear Limited | Implant tool |
USD982745S1 (en) | 2019-10-25 | 2023-04-04 | Cochlear Limited | Implant tool |
EP4017030A1 (en) | 2020-12-18 | 2022-06-22 | CADskills | Device for coupling a bone conduction vibrator |
Also Published As
Publication number | Publication date |
---|---|
US7116794B2 (en) | 2006-10-03 |
EP1820368B1 (en) | 2010-06-30 |
AU2005305125A1 (en) | 2006-05-18 |
US20060126874A1 (en) | 2006-06-15 |
DE05818388T1 (en) | 2008-05-21 |
DK1820368T3 (en) | 2010-10-11 |
WO2006052527A3 (en) | 2006-06-22 |
EP1820368A4 (en) | 2009-12-23 |
CN101057525B (en) | 2012-04-18 |
CN101057525A (en) | 2007-10-17 |
EP1820368A2 (en) | 2007-08-22 |
DE602005022104D1 (en) | 2010-08-12 |
WO2006052527B1 (en) | 2006-08-03 |
AU2005305125B2 (en) | 2010-12-16 |
WO2006052527A2 (en) | 2006-05-18 |
ATE472904T1 (en) | 2010-07-15 |
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